Targeted Illumination For Surgical Instrument

ABSTRACT

An illuminated surgical instrument has a working area located near an end of the instrument. An array of optical fibers terminates near the end of the instrument. The array of optical fibers is located adjacent to the instrument such that the array of optical fibers provides targeted illumination to the working area only on one side of the instrument.

BACKGROUND OF THE INVENTION

The present invention relates to an illuminated vitrectomy probe orother illuminated ophthalmic surgical instrument, and more particularlyto an optical fiber array configuration designed to provide illuminationover a specific area at the working end of an instrument, for example,the cutting port of a vitrectomy probe.

Anatomically, the eye is divided into two distinct parts—the anteriorsegment and the posterior segment. The anterior segment includes thelens and extends from the outermost layer of the cornea (the cornealendothelium) to the posterior of the lens capsule. The posterior segmentincludes the portion of the eye behind the lens capsule. The posteriorsegment extends from the anterior hyaloid face to the retina, with whichthe posterior hyaloid face of the vitreous body is in direct contact.The posterior segment is much larger than the anterior segment.

The posterior segment includes the vitreous body—a clear, colorless,gel-like substance. It makes up approximately two-thirds of the eye'svolume, giving it form and shape before birth. It is composed of 1%collagen and sodium hyaluronate and 99% water. The anterior boundary ofthe vitreous body is the anterior hyaloid face, which touches theposterior capsule of the lens, while the posterior hyaloid face formsits posterior boundary, and is in contact with the retina. The vitreousbody is not free-flowing like the aqueous humor and has normal anatomicattachment sites. One of these sites is the vitreous base, which is a3-4 mm wide band that overlies the ora serrata. The optic nerve head,macula lutea, and vascular arcade are also sites of attachment. Thevitreous body's major functions are to hold the retina in place,maintain the integrity and shape of the globe, absorb shock due tomovement, and to give support for the lens posteriorly. In contrast toaqueous humor, the vitreous body is not continuously replaced. Thevitreous body becomes more fluid with age in a process known assyneresis. Syneresis results in shrinkage of the vitreous body, whichcan exert pressure or traction on its normal attachment sites. If enoughtraction is applied, the vitreous body may pull itself from its retinalattachment and create a retinal tear or hole.

Various surgical procedures, called vitreo-retinal procedures, arecommonly performed in the posterior segment of the eye. Vitreo-retinalprocedures are appropriate to treat many serious conditions of theposterior segment. Vitreo-retinal procedures treat conditions such asage-related macular degeneration (AMD), diabetic retinopathy anddiabetic vitreous hemorrhage, macular hole, retinal detachment,epiretinal membrane, CMV retinitis, and many other ophthalmicconditions.

A surgeon performs vitreo-retinal procedures with a microscope andspecial lenses designed to provide a clear image of the posteriorsegment. Several tiny incisions just a millimeter or so in length aremade on the sclera at the pars plana. The surgeon inserts microsurgicalinstruments through the incisions such as a fiber optic light source toilluminate inside the eye, an infusion line to maintain the eye's shapeduring surgery, and instruments to cut and remove the vitreous body(such as a vitrectomy probe—which has a cutting end that is insertedinto the eye. A vitrectomy probe has a small gauge needle or cannulawith a cutting mechanism on the end that is inserted into the eye).

During such surgical procedures, proper illumination of the inside ofthe eye is important. Typically, a thin optical fiber is inserted intothe eye to provide the illumination. A light source, such as a metalhalide lamp, a halogen lamp, a xenon lamp, or a mercury vapor lamp, isoften used to produce the light carried by the optical fiber into theeye. The light passes through several optical elements (typicallylenses, mirrors, and attenuators) and is launched at an optical fiberthat carries the light into the eye.

To reduce the number of required incisions during vitrectomy surgery andimprove the delivery of light to the surgical site, an effort has beenmade to integrate a light source (typically one or more optical fibers)with a vitrectomy probe. These efforts have been difficult because ofthe small diameters of vitrectomy probes. It is desirable to make thediameter of the cutting end of the vitrectomy probe as small as possibleso that it can be inserted through very small incisions into the eye.

In one case, a ring of optical fibers is disposed around a vitrectomyprobe and held in place by a sleeve. This illuminated vitrectomy sleeveconsists of a bundle of small diameter optical fibers fed into a hubregion and then distributed in a ring pattern. The illuminatedvitrectomy sleeve is designed to be a stand-alone device into which thevitrectomy probe is inserted. As such, it must have its own structuralstrength that is provided by a sandwiching the array of optical fibersbetween two metal or plastic cylindrical cannulas. Since it ispreferable to make the total diameter of the vitrectomy probe and sleeveas small as possible, very little cross-sectional area is left to housethe optical fibers. Accordingly, very little light is transmitted intothe eye. In addition, the ring of fibers distributes light throughputthe entire region adjacent to the distal end of the vitrectomy probeinstead of concentrating it on the cutting port opening where it isneeded.

In another case, a single fiber may be attached to the vitrectomy needleand held in place with a plastic sleeve. For example, Synergetics, Inc.manufactures a 25 gauge vitrectomy needle with a single optical fiberthat is held in place with a plastic sleeve. The plastic sleeve can thenfit into a 20 gauge cannula that is inserted into the eye. Very littlecross-sectional area is available between the 25 gauge vitrectomy needleand the inner surface of the plastic sleeve (which is typically one ortwo mils thick). In addition, a larger incision must be made toaccommodate the 20 gauge cannula through which the plastic sleeve mustfit. Today, it is preferable to keep the incision size small so as toaccommodate a probe with a diameter of 23 gauge or smaller. What isneeded is an improved illuminated vitrectomy probe that deliverssufficient light into the eye while accommodating these smaller incisionsizes.

In addition, the same constraints restrict the feasible size of otherophthalmic surgical instruments. For example, scissors, forceps,aspiration probes, retinal picks, delamination spatulas, variouscannulas, and the like may also benefit from targeted illumination.These instruments are designed to fit through small gauge cannulas thatare inserted through the sclera during surgery. The same principles usedto design an improved illuminated vitrectomy probe can also be used toprovide targeted illumination for these other surgical instruments.

SUMMARY OF THE INVENTION

In one embodiment consistent with the principles of the presentinvention, the present invention is an illuminated vitrectomy probe. Thevitrectomy probe has a cutting port disposed at a distal end of acannula. An array of optical fibers terminates near the cutting port.The array of optical fibers is located adjacent to the cannula only on aside of the cannula on which the cutting port is located.

In another embodiment consistent with the principles of the presentinvention, the present invention is an illuminated surgical instrument.The instrument has a working area located near an end of the instrument.An array of optical fibers terminates near the end of the instrument.The array of optical fibers is located adjacent to the instrument suchthat the array of optical fibers provides illumination to the workingarea only on one side of the instrument.

In another embodiment consistent with the principles of the presentinvention, the present invention is an illuminated surgical instrument.The instrument has a working area located near an end of the instrument.The working area has an orientation with respect to the end of theinstrument. An array of optical fibers terminates near the end of theinstrument. The array of optical fibers is located adjacent to theinstrument such that the array of optical fibers provides targetedillumination only to the working area. The targeted illumination isconfigured for the orientation of the working area.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary and explanatory onlyand are intended to provide further explanation of the invention asclaimed. The following description, as well as the practice of theinvention, set forth and suggest additional advantages and purposes ofthe invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of this specification, illustrate several embodiments of theinvention and together with the description, serve to explain theprinciples of the invention.

FIG. 1 is an unfolded view of an ophthalmic endoilluminator according toan embodiment of the present invention.

FIGS. 2A and 2B are perspective views of a vitrectomy probe according toan embodiment of the present invention.

FIG. 3A is a cross section view of a vitrectomy hand piece with anintegrated illuminator according to an embodiment of the presentinvention.

FIG. 3B is an exploded cross section view of a vitrectomy hand piecewith an integrated illuminator according to an embodiment of the presentinvention.

FIG. 4 is a cross section view of an illuminator optical fiber pathaccording to an embodiment of the present invention.

FIG. 5 is a cross section view of a distal end of an illuminatedvitrectomy probe according to an embodiment of the present invention.

FIG. 6 is a cross section view of an optical fiber array used with anilluminated vitrectomy probe according to an embodiment of the presentinvention.

FIG. 7 is a cross section view of a distal end of an illuminatedvitrectomy probe according to an embodiment of the present invention.

FIG. 8 is a cross section view of an optical fiber array used with anilluminated vitrectomy probe according to an embodiment of the presentinvention.

FIG. 9A is side view of an illuminated vitrectomy probe according to anembodiment of the present invention.

FIG. 9B is top view of an illuminated vitrectomy probe according to anembodiment of the present invention.

FIG. 10A is side view of a pair of illuminated endo-ophthalmic forcepsaccording to an embodiment of the present invention.

FIG. 10B is top view of a pair of illuminated endo-ophthalmic forcepsaccording to an embodiment of the present invention.

FIG. 11 is a cross section view of an optical fiber array used with asurgical instrument with a generally circular cross section according toan embodiment of the present invention.

FIG. 12 is a cross section view of an optical fiber array used with asurgical instrument with a generally elliptical cross section accordingto an embodiment of the present invention.

FIG. 13 is a cross section view of an optical fiber array used with asurgical instrument with a generally elliptical cross section accordingto an embodiment of the present invention.

FIG. 14 is a cross section view of an optical fiber array used with asurgical instrument with a generally rectangular cross section accordingto an embodiment of the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Reference is now made in detail to the exemplary embodiments of theinvention, examples of which are illustrated in the accompanyingdrawings. Wherever possible, the same reference numbers are usedthroughout the drawings to refer to the same or like parts.

FIG. 1 is an unfolded view of an ophthalmic endoilluminator as used withan illuminated vitrectomy probe according to an embodiment of thepresent invention. In FIG. 1, the endoilluminator includes light source105, collimating lens 110, optional cold mirror 115, optional hot mirror116, attenuator 120, condensing lens 125, connector 150, optical fiber155, hand piece 160, and vitrectomy probe 165.

The light from light source 105 is collimated by collimating lens 110.The collimated light is reflected and filtered by optional cold mirror115 and/or transmitted and filtered by optional hot mirror 116. Theresulting beam is attenuated by attenuator 120 and focused by condensinglens 125. The focused beam is directed through connector 150 and opticalfiber 155 to vitrectomy probe 165 where it illuminates the inside of theeye as described below.

Light source 105 is typically a lamp, such as a mercury vapor lamp, axenon lamp, a metal halide lamp, or a halogen lamp. Light source 105 isoperated at or near full power to produce a relatively stable andconstant light output. In one embodiment of the present invention, lightsource 105 is a xenon lamp with an arc length of about 0.18 mm. Otherembodiments of the present invention utilize other light sources such aslight emitting diodes (LEDs). One or more LEDs can be operated toproduce a constant and stable light output. As is known, there are manytypes of LEDs with different power ratings and light output that can beselected as light source 105.

Collimating lens 110 is configured to collimate the light produced bylight source 105. As is commonly known, collimation of light involveslining up light rays. Collimated light is light whose rays are parallelwith a planar wave front.

Optional cold mirror 115 is a dichroic reflector that reflects visiblewavelength light and only transmits infrared and ultraviolet light toproduce a beam filtered of harmful infrared and ultraviolet rays.Optional hot mirror 116 reflects long wavelength infrared light andshort wavelength ultraviolet light while transmitting visible light. Theeye's natural lens filters the light that enters the eye. In particular,the natural lens absorbs blue and ultraviolet light which can damage theretina. Providing light of the proper range of visible light wavelengthswhile filtering out harmful short and long wavelengths can greatlyreduce the risk of damage to the retina through aphakic hazard, bluelight photochemical retinal damage and infrared heating damage, andsimilar light toxicity hazards. Typically, a light in the range of about430 to 700 nanometers is preferable for reducing the risks of thesehazards. Optional cold mirror 115 and optional hot mirror 116 areselected to allow light of a suitable wavelength to be emitted into aneye. Other filters and/or dichroic beam splitters may also be employedto produce a light in this suitable wavelength range. For example,holographic mirrors may also be used to filter light.

Attenuator 120 attenuates or decreases the intensity of the light beam.Any number of different attenuators may be used. For example, mechanicallouvers, camera variable aperture mechanisms, or neutral density filtersmay be used. A variable-wedge rotating disk attenuators may also beused.

Condensing lens 125 focuses the attenuated light beam so that it can belaunched into a small diameter optical fiber. Condensing lens 125 is alens of suitable configuration for the system. Condensing lens 125 istypically designed so that the resulting focused beam of light can besuitably launched into and transmitted by an optical fiber. As iscommonly known, a condensing lens may be a biconvex or plano-convexspherical or aspheric lens. In a plano-convex aspheric lens, one surfaceis planar and the other surface is convex with a precise asphericsurface in order to focus the light to a minimum diameter spot.

The endoilluminator that is handled by the ophthalmic surgeon includesconnector 150, optical fiber 155, hand piece 160, and illuminatedvitrectomy probe 165. Connector 150 is designed to connect the opticalfiber 155 to a main console (not shown) containing light source 105.Connector 150 properly aligns optical fiber 155 with the beam of lightthat is to be transmitted into the eye. Optical fiber 155 is typically asmall diameter fiber that may or may not be tapered. Hand piece 160 isheld by the surgeon and allows for the manipulation of illuminatedvitrectomy probe 165 in the eye.

FIGS. 2A and 2B are perspective views of a vitrectomy probe according toan embodiment of the present invention. In a typical vitrectomy probe,an outer cannula 205 includes port 210. An inner piston 215 reciprocatesin cannula 205. One end of piston 215 is configured so that it can cutvitreous when as it enters port 210. As shown in FIGS. 2A and 2B, piston215 moves up and down in cannula 205 to produce a cutting action.Vitreous enters port 210 when the vitrectomy probe is in the positionshown in FIG. 2A. The vitreous is cut as piston 215 moves upward closingoff port 210 as shown in FIG. 2B. While most of the details of avitrectomy probe are omitted, it is important to note that the cuttingof the vitreous takes place at port 210. Accordingly, it would bedesirable to concentrate illumination around port 210, so that a surgeoncan see the vitreous being cut (as well as other eye structures near thecutting mechanism).

FIG. 3A is a cross section view of a vitrectomy hand piece with anintegrated illuminator according to an embodiment of the presentinvention. In FIG. 3A, an array of optical fibers 310 is located invitrectomy hand piece housing 305. Optical fiber array 310 exits thehand piece housing 305 at a small opening adjacent to cannula 315.Cannula 315 is similar in structure and operation to cannula 205 ofFIGS. 2A and 2B.

FIG. 3B is an exploded cross section view of a vitrectomy hand piecewith an integrated illuminator according to an embodiment of the presentinvention. FIG. 3B more clearly shows the orientation of optical fiberarray 310 with respect to hand piece housing 305 and cannula 315.Optical fiber array 310 exits hand piece housing 305 through a smallopening adjacent to cannula 315. Optical fiber array 310 is arranged ata distal end of cannula 315 as depicted in FIGS. 5, 7, 9A, and 9B. Thesmall opening in hand piece housing 305 through which optical fiberarray 310 passes may be sealed.

FIG. 4 is cross section view of an illuminator optical fiber pathaccording to an embodiment of the present invention. In the embodimentof FIG. 4, a standard 20 gauge ACMI connector 405 is coupled to aproximally belled. 0.0295 inch, 0.5 NA or 0.63 NA optical fiber 410.Optical fiber 410 is coupled to a belled, stretched 0.63 NA opticalfiber 420 via a 25 gauge coupling 415. A second coupling 425 couplesoptical fiber 420 to an array of optical fibers 430. While a specificexample is provided in FIG. 4, numerous other configurations of opticalfibers and couplers may be employed to implement the illuminatedvitrectomy probe of the present invention.

FIG. 5 is cross section view of a distal end of an illuminatedvitrectomy probe according to an embodiment of the present invention.FIG. 5 shows the arrangement of an array of optical fibers at a distalor cutting end of a vitrectomy probe. This arrangement of optical fibersis designed to produce illumination at the cutting port of a vitrectomyprobe. The view in FIG. 5 is a cross section view or slice of thevitrectomy probe perpendicular to the axis along which the cannula lies.In this example, seven optical fibers 510, 515, 520, 525, 530, 535, and540 (or optical fiber array) are arranged around vitrectomy probe 505 asshown. In the embodiment of FIG. 5, optical fiber array 510, 515, 520,525, 530, 535, and 540 is potted into place against the upper surface ofvitrectomy probe needle 505. Vitrectomy probe 505, in this case, is a 25gauge probe—that is, its cannula is a 25 gauge cannula. The dashedcircle represents a 23 gauge cannula through which the vitrectomy probe505 and optical fiber array (seven optical fibers—510, 515, 520, 525,530, 535, and 540) pass in order to enter the eye. In this manner, thevitrectomy cutting function and the illumination function—both of whichare required for surgery—are provided in a small diameter package thatfits through a 23 gauge cannula. This small 23 gauge cannula isdesirable because smaller incision sizes in the eye generally result infewer complications.

In the embodiment of FIG. 5, optical fiber array 510, 515, 520, 525,530, 535, and 540 is comprised of fibers ranging in size from 0.00345inches in diameter (535 and 540) to 0.0049 inches in diameter (510).Optical fibers 515 and 520 have a diameter of 0.0047 inches, and opticalfibers 525 and 530 have a diameter of 0.00415 inches. In this case,optical fiber array 510, 515, 520, 525, 530, 535, and 540 provides across section area available for illumination of about 60,500 squaremicrons. As such, this configuration emits about 16 lumens (using anAHBI illuminator with 100% efficiency at the coupling)—all of which isconcentrated around the cutting port of the vitrectomy probe.

FIG. 6 is a cross section view of an optical fiber array used with anilluminated vitrectomy probe according to an embodiment of the presentinvention. The embodiment of FIG. 6 depicts the proximal end of opticalfiber array 510, 515, 520, 525, 530, 535, and 540. This end of opticalfiber array 510, 515, 520, 525, 530, 535, and 540 is coupled to the 0.63NA optical fiber 420 as depicted in FIG. 4. In FIG. 6, 605 representsthe diameter of the 0.63 NA optical fiber core. Each of the opticalfibers in optical fiber array 510, 515, 520, 525, 530, 535, and 540typically have a core and cladding. In FIG. 6, the proximal end of theoptical fiber cores of optical fiber array 510, 515, 520, 525, 530, 535,and 540 fit within 605 (representing the core of the 0.63 NA opticalfiber).

FIG. 7 is a cross section view of a distal end of an illuminatedvitrectomy probe according to an embodiment of the present invention. Inthe embodiment of FIG. 7, a sleeve 750 (in this case a polyimide sleevewith a 1 mil thickness—though any sleeve may be used) holds opticalfiber array 710, 715, 720, 725, 730, 735, and 740 in place againstvitrectomy probe 705. Sleeve 750 is secured to vitrectomy probe 705 withan adhesive, such as an optical adhesive. The embodiment of FIG. 7 isalso designed to fit through a 23 gauge cannula. However, sleeve 750takes up some of the cross section area requiring the optical fibers inoptical fiber array 710, 715, 720, 725, 730, 735, and 740 to havesmaller diameters. In this embodiment, Optical fiber 710 has a diameterof 0.0041 inches, optical fibers 715 and 720 have diameters of 0.0039inches, optical fibers 725 and 730 have diameters of 0.0035 inches, andoptical fibers 735 and 740 have diameters of 0.0029 inches. Theresulting cross section area (about 42,400 microns) provides a luminousflux of about 11.5 (using an AHBI illuminator with 100% efficiency atcoupling). As in FIG. 5, all of this light is concentrated around thecutting port of the vitrectomy probe.

FIG. 8 is cross section view of an optical fiber array used with anilluminated vitrectomy probe according to an embodiment of the presentinvention. The embodiment of FIG. 6 depicts the proximal end of opticalfiber array 710, 715, 720, 725, 730, 735, and 740. This end of opticalfiber array 710, 715, 720, 725, 730, 735, and 740 is coupled to the 0.63NA optical fiber 420 as depicted in FIG. 4. Optional cladding orsheathing 805 is also depicted.

FIG. 9A is side view of an illuminated vitrectomy probe according to anembodiment of the present invention, and FIG. 9B is top view of anilluminated vitrectomy probe according to an embodiment of the presentinvention. FIGS. 9A and 9B provide a different view of the arrangementof the optical fibers shown in FIGS. 5 and 7. Port 910 is located nearthe end of cannula 905. Port 910 is the cutting port of a vitrectomyprobe. Accordingly, concentrating light around port 910 is desirablebecause it allows the surgeon to see the eye structures near the cuttingmechanism of the vitrectomy probe. Conversely, light that is notconcentrated around port 910 is wasted.

In the embodiment of FIGS. 9A and 9B, an optical fiber array has sevenoptical fibers 915, 920, 925, 930, 935, 940, and 945. The seven opticalfibers 915, 920, 925, 930, 935, 940, and 945 of the optical fiber arrayare arranged around the top of cannula 905 near port 910. Optical fiber915 has the largest diameter, and optical fibers 930 and 945 have thesmallest diameters. The diameters of optical fibers 925 and 940 arelarger than the diameters of optical fibers 930 and 945 and smaller thanthe diameters of optical fibers 920 and 935. The diameters of opticalfibers 920 and 935 are larger than the diameters of optical fibers 925and 940 and smaller than the diameter of optical fiber 915. Thisarrangement has been found to provide a sufficient amount of light nearthe cutting port 910 of a vitrectomy probe, while maintaining a small(23 gauge) profile.

While the examples provided herein describe an illuminated vitrectomyprobe that fits through a 23 gauge cannula, it will be appreciated thatthe same arrangement of a vitrectomy probe and optical fiber array canbe applied to cannulas of other sizes. For example, an optical fiberarray of seven fibers can be arranged around a vitrectomy probe in thesame way described herein to fit through a 20 gauge cannula, or eventhrough cannulas smaller than 23 gauge. For example, as the diameter ofa vitrectomy probe decreases, more cross section area is available forillumination. An illuminated vitrectomy probe that fits through a 25gauge cannula can have the same optical fiber array configurationdescribed herein.

More generally, the same principles described with respect to theilluminated vitrectomy probe of the preceding figures can be applied toany surgical instrument designed to fit through a small gauge cannula.For example, in ophthalmic surgery, scissors, forceps, aspirationprobes, retinal picks, delamination spatulas, various cannulas, and thelike may also benefit from targeted illumination. These instruments aredesigned to fit through small gauge cannulas that are inserted throughthe sclera during ophthalmic surgery. For each of these instruments,targeted illumination around the working end of the instrument isbeneficial.

For example, FIG. 10A is side view of illuminated endo-ophthalmicforceps according to an embodiment of the present invention, and FIG.10B is a top view of illuminated endo-ophthalmic forceps according to anembodiment of the present invention. FIGS. 10A and 10B provide a view ofthe arrangement of the optical fibers for forceps that is similar tothat described with respect to the illuminated vitrectomy probe of FIGS.5-9. Forceps 1010 include a pair of jaws that are designed to movetogether to hold eye tissues. Accordingly, targeting light aroundforceps 1010 is desirable because it allows the surgeon to see the eyestructures near the holding mechanism of the forceps. In the embodimentof FIGS. 10A and 10B, light is concentrated on one side of the forceps1010 as shown, so that a surgeon can more easily see the structure thatis located between the jaws of the forceps. Alternatively, the opticalfibers 915, 920, 925, 930, 935, 940, and 945 can be positioned toprovide backlighting, for example, to provide illumination on theretina.

In the embodiment of FIGS. 10A and 10B, an optical fiber array has sevenoptical fibers 915, 920, 925, 930, 935, 940, and 945. The seven opticalfibers 915, 920, 925, 930, 935, 940, and 945 of the optical fiber arrayare arranged around the top of forceps 1010. Optical fiber 915 has thelargest diameter, and optical fibers 930 and 945 have the smallestdiameters. The diameters of optical fibers 925 and 940 are larger thanthe diameters of optical fibers 930 and 945 and smaller than thediameters of optical fibers 920 and 935. The diameters of optical fibers920 and 935 are larger than the diameters of optical fibers 925 and 940and smaller than the diameter of optical fiber 915. This arrangement hasbeen found to provide a sufficient amount of light near the working endof the forceps 1010, while maintaining a small (23 gauge) profile. Inthis case, forceps 1010, like vitrectomy probe cannula 905, has acircular cross section.

The same arrangement of optical fibers can be applied to any surgicalinstrument with a generally circular cross section. In this manner,illumination can be targeted to a certain area (typically the workingend of the instrument considering the orientation of the instrument inthe eye) to provide light where it is needed. For example, in ophthalmicsurgery, scissors, forceps, aspiration probes, retinal picks,delamination spatulas, various cannulas, and the like may benefit fromtargeted illumination. Providing light to the working area of theinstrument or to the eye structure with which the instrument interfacesallows the surgeon to better see during surgery.

FIG. 11 is a cross section view of an optical fiber array used with asurgical instrument with a generally circular cross section according toan embodiment of the present invention. In FIG. 11, generally circularinstrument 1100 (represented by a circle) must fit through a small gaugecannula 1110 (also represented by a circle) in order to enter the eye.The radius of the cannula, r₁, is larger than the radius of theinstrument, r₂. The available area for illumination is easilycalculated: π(r₁ ²−r₂ ²). In this case, this area is best used forillumination by locating instrument 1100 on an interior surface ofcannula 1110 as shown. The largest optical fiber that can then fit inthe resulting volume is optical fiber 1150. The center point of opticalfiber 1150 and the center point of instrument 1100 lie along the sameline in FIG. 11 (dotted line). The circle representing optical fiber1150 is tangential to the circle representing instrument 1100 and thecircle representing cannula 1110. Specific measurements depend on thediameter of instrument 1100 and cannula 1110.

With the first optical fiber 1150 in place, subsequent optical fibers,such as optical fiber 1155, can be positioned. In this example, thelargest possible diameter optical fibers are used to fill the availablespace between the outside of instrument 1100 and the inside of cannula1110. Generally larger diameter optical fibers have greater capacity fortransporting luminous flux through the fiber. With optical fiber 1150 inplace, optical fiber 1155 is positioned such that the circlerepresenting it is tangential to the circle representing optical fiber1150, the circle representing instrument 1100, and the circlerepresenting cannula 1110. This is most easily done using a CAD-typedrawing program to approximate the diameter of optical fiber 1155. Thesize and position of other optical fibers can be determined in a likemanner.

FIG. 12 is a cross section view of an optical fiber array used with asurgical instrument with a generally elliptical cross section accordingto an embodiment of the present invention. The same principles describedwith respect to the generally circular instrument of FIG. 11 also applyto the generally elliptical instrument of FIG. 12. Instrument 1200,represented by an ellipse, is located in small gauge cannula 1210 sothat the area between instrument 1200 and cannula 1210 is maximized onone side and minimized on the other. In this position, instrument 1200contacts the interior surface of cannula 1210 along two lines containedalong the cylinder of cannula 1210. With the location of instrument 1200fixed, the circle representing optical fiber 1250 is located such thatit is tangential to the ellipse representing instrument 1200 and thecircle representing cannula 1210. The diameter of the circlerepresenting optical fiber 1250 and the minor diameter of the ellipserepresenting instrument 1200 lie along the same line (dotted line).

FIG. 13 is a cross section view of an optical fiber array used with asurgical instrument with a generally elliptical cross section accordingto an embodiment of the present invention. In the embodiment of FIG. 13,targeted illumination is provided in two locations. Optical fibers 1350and 1355 (and others not shown) provide illumination on top ofinstrument 1300, while optical fibers 1360 and 1365 (and others notshown) provide illumination on top of instrument 1300. Cannula 1310 isalso depicted. The optical fibers are selected and positioned using thesame principles described above.

FIG. 14 is a cross section view of an optical fiber array used with asurgical instrument with a generally rectangular cross section accordingto an embodiment of the present invention. Again, two areas are targetedfor illumination. Optical fibers 1450 and 1455 (and others not shown)provide illumination on top of instrument 1400, while optical fibers1460 and 1465 (and others not shown) provide illumination on top ofinstrument 1400. Cannula 1410 is also depicted. The optical fibers areselected and positioned using the same principles described above.

The same principles can be applied to an instrument of any crosssection. In addition, instruments may be approximated by geometricalshapes. For example, an instrument that has an oblong cross section canbe approximated by an ellipse. Of course, the location of the targetedillumination corresponds to the location of the optical fibers. Whilethe fibers are generally selected to maximize light throughput, theirlocation can be adjusted for a given instrument. Further, while theoptical fibers are depicted as having a generally circular crosssection, optical fibers and light guides with other cross sections mayalso be employed.

From the above, it may be appreciated that the present inventionprovides an improved illuminated vitrectomy probe. Arranging an array ofoptical fibers near the working area of a surgical instrument provideslight that is usable by the surgeon during surgery. In addition, thepresent invention most effectively utilizes the small cross sectionalarea available to carry an optical fiber array. The present invention isillustrated herein by example, and various modifications may be made bya person of ordinary skill in the art.

Other embodiments of the invention will be apparent to those skilled inthe art from consideration of the specification and practice of theinvention disclosed herein. It is intended that the specification andexamples be considered as exemplary only, with a true scope and spiritof the invention being indicated by the following claims.

1. An illuminated vitrectomy probe comprising: a vitrectomy probe havinga cutting port disposed at a distal end of a cannula; and an array ofoptical fibers terminating near the cutting port, the array of opticalfibers located adjacent to the cannula only on a side of the cannula onwhich the cutting port is located.
 2. The illuminated vitrectomy probeof claim 1 wherein the array of optical fibers and cannula areconfigured to fit through a second cannula with a size not greater than23 gauge.
 3. The illuminated vitrectomy probe of claim 2 in which thearray of optical fibers comprises seven optical fibers with diametersbetween 0.003 inches and 0.005 inches.
 4. The illuminated vitrectomyprobe of claim 1 wherein the array of optical fibers comprises opticalfibers with diameters between 0.003 inches and 0.005 inches.
 5. Theilluminated vitrectomy probe of claim 1 further comprising: a pottingsubstance that holds the optical fibers against the cannula of thevitrectomy probe.
 6. The illuminated vitrectomy probe of claim 1 furthercomprising: a sleeve that holds the optical fibers against the cannulaof the vitrectomy probe.
 7. The illuminated vitrectomy probe of claim 6wherein the array of optical fibers comprises optical fibers withdiameters between 0.002 inches and 0.005 inches.
 8. The illuminatedvitrectomy probe of claim 1 further comprising: a housing having anopening through which the array of optical fibers passes, the housingattached to the cannula.
 9. The illuminated vitrectomy probe of claim 1wherein the array of optical fibers are disposed in a semi-circularpattern around the cannula near the cutting port.
 10. The illuminatedvitrectomy probe of claim 1 further comprising: a coupling for couplingan end of the array of optical fibers to a light source.
 11. Anilluminated surgical instrument comprising: an instrument with a workingarea located near an end of the instrument; an array of optical fibersterminating near the end of the instrument, the array of optical fiberslocated adjacent to the instrument such that the array of optical fibersprovides illumination to the working area only on one side of theinstrument.
 12. The illuminated surgical instrument of claim 11 whereinthe plurality of optical fibers and instrument are configured to fitthrough a cannula with a size not greater than 23 gauge.
 13. Theilluminated surgical instrument of claim 11 wherein the plurality ofoptical fibers comprises optical fibers with diameters between 0.003inches and 0.005 inches.
 14. The illuminated surgical instrument ofclaim 11 further comprising: a potting substance that holds theplurality of optical fibers against the instrument.
 15. The illuminatedsurgical instrument of claim 11 further comprising: a sleeve that holdsthe plurality of optical fibers against the instrument.
 16. Theilluminated surgical instrument of claim 15 wherein the plurality ofoptical fibers comprises optical fibers with diameters between 0.002inches and 0.005 inches.
 17. The illuminated surgical instrument ofclaim 11 wherein the array of optical fibers is arranged to providetargeted illumination to the working area of the instrument and, thetargeted illumination configured for an orientation of the working area.18. An illuminated surgical instrument comprising: an instrument with aworking area located near an end of the instrument, the working areahaving an orientation with respect to the end of the instrument; anarray of optical fibers terminating near the end of the instrument, thearray of optical fibers located adjacent to the instrument such that thearray of optical fibers provides targeted illumination only to theworking area, the targeted illumination configured for the orientationof the working area.
 19. The illuminated surgical instrument of claim 18wherein the plurality of optical fibers and instrument are configured tofit through a cannula with a size not greater than 23 gauge.
 20. Theilluminated surgical instrument of claim 18 further comprising: apotting substance that holds the plurality of optical fibers against theinstrument.
 21. The illuminated surgical instrument of claim 18 furthercomprising: a sleeve that holds the plurality of optical fibers againstthe instrument.